Haptic devices for intraocular lens

The inventive is directed to a haptic for fixation to, and manufacture in conjunction with, an intraocular lens to be implanted in the natural lens capsule of the human eye. The haptic secures the lens in an appropriate position within the natural capsule so as to provide optimal visual acuity through the aphakic lens. The haptic ends are designed to position the lens neutrally, anteriorly or posteriorly within the lens envelope. At the connection point of the ribbon portion to the solid end plate of the haptic, the haptic may be notched to facilitate compressing the lens into its injector for insertion into the eye through an incision in the cornea. Once compressed and passed through the cornea, the implanted lens will be secured by the haptics in the lens capsule once all possible natural lens material and epithelial cells have been removed.

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Description
REFERENCE TO RELATED APPLICATIONS

This application claims priority to U.S. Provisional Application No. 61/118,085 of the same title and filed Nov. 26, 2008, U.S. Provisional Application No. 61/157,781 of the same title and filed Mar. 5, 2009, and U.S. Provisional Application No. 61/184,655 of the same title and filed Jun. 5, 2009, the entirety of each of which is hereby incorporated by reference.

BACKGROUND

1. Field of the Invention

This invention is directed to haptic devices for intraocular lenses that provide increased comfort and performance to a patient. In particular, the invention is directed to haptic devices and designs, including injectors, for insertion of intraocular lenses without rolling the lenses, and to methods for performing insertion. Specifically, the invention, along with its various iterations, is designed to provide suitable degrees of focal flexibility, or accommodation, when used in conjunction with a monofocal optic, and, in certain instances, mitigate the onset of post-surgical conditions, specifically posterior capsular Opacification.

2. Description of the Background

An intraocular lens (IOL) is an implanted lens in the eye, usually replacing the existing crystalline lens because it has been clouded over by a cataract, or as a form of refractive surgery to change the eye's optical power. The whole device usually comprises a small plastic lens with plastic side struts, called haptics, to hold the lens in place within the capsular bag inside the eye. Haptics also form the means of attachment of lenses to other areas of the eye, including the anterior angle or sulcus, the iris, and the posterior chamber ciliary sulcus. IOLs were traditionally made of an inflexible material (e.g. PMMA) though this largely been superseded by the use of flexible materials. Most IOLs fitted today are fixed monofocal lenses matched to distance vision. However, other types are available, such as multifocal IOLs which provide the patient with multiple-focused vision at far and reading distance, tonic IOLs to correct for astigmatisms, and adaptive IOLs which provide the patient with limited visual accommodation.

Intraocular lenses have been used since 1999 for correcting larger errors in myopic (near-sighted), hyperopic (far-sighted), and astigmatic eyes. This type of IOL is also called PIOL (phakic intraocular lens), and the crystalline lens is not removed. More commonly, aphakic IOLs (that is, not PIOLs) are now used for visual correction errors (especially substantial hyperopia), and implanted via Clear Lens Extraction and Replacement (CLEAR) surgery. During CLEAR, the crystalline lens is extracted and an IOL replaces it in a process that is very similar to cataract surgery: both involve lens replacement, local anesthesia, both last approximately 30 minutes, and both require making a small incision in the eye for lens insertion. Patients recover from CLEAR surgery 1-7 days after the operation. During this time, patients should avoid strenuous exercise or any activity that significantly raises blood pressure. Patients should also visit their ophthalmologists regularly for several months so as to monitor the IOL implants. CLEAR has a 90% success rate (risks include wound leakage, infection, inflammation, and astigmatism). CLEAR can only be performed on patients ages 40 and older. This is to ensure that eye growth, which disrupts IOL lenses, will not occur post-surgery.

Once implanted, IOL lenses have three major benefits. First, they are an alternative to LASIK, a form of eye surgery that does not work for people with serious vision problems. Second, effective IOL implants may eliminate the need for glasses or contact lenses post-surgery. Third, the cataract will not return, as the lens has been removed. The disadvantage is that the eye's ability to change focus (accommodate) may have been reduced or eliminated, depending on the kind of lens implanted.

While significant advances have been made in the optical quality of aphakic lenses, most lenses currently made have an overall optical thickness of one millimeter or greater at the center optical focal point (e.g. see U.S. Pat. No. 4,363,142). In the late 1990's, two patents were applied for and subsequently issued for lens optics significantly thinner than the afore-referenced lens patents (U.S. Pat. Nos. 6,096,077 and 6,224,628). Although improved, the extreme thinness of the lens manufactured in accordance with U.S. Pat. No. 6,096,077 caused some minor distortions of the optic once in the eye, while the lens manufactured in accordance with U.S. Pat. No. 6,224,628 was poured of molded silicone and did not provide the desired visual acuity.

Generally, the lens separates the aqueous humor from the vitreous body. The iris separates the region between the cornea or anterior of the eye and the lens into an anterior chamber and a posterior chamber. The lens itself is contained in a membrane known as the capsule or capsular sac. When the lens is removed from the eye, the capsule may also be removed (intracapsular extraction), or the anterior portion of the capsule may be removed with the lens leaving the posterior portion of the capsule intact (extracapsular extraction), often leaving small folds or flaps from the anterior portion of the capsule. In an intraocular implant, the artificial or prosthetic lens may be inserted in the anterior chamber, the posterior chamber, or the capsular sac. The artificial lenses are usually fixedly attached within the eye, either by stitching to the iris, or by some supporting means or arms attached to the lens; in all cases the fixation mechanisms are categorized as haptics.

Several intraocular lenses designed for implant in the anterior chamber feature haptics with feet which support the lens in order to avoid the need for clips or sutures to secure the lens to the iris. The lenses worked; however, sizing the lens to fit the eye was critical to avoid complications. The lenses were made in lengths from 11.5 mm to 14 mm in 0.5 mm increments, and the thickness of the feet was about 250 microns.

A variety of lenses has been developed that provides up to four point support for the lens. The support structures for these haptics are often linked to the lens body so that the support structure should not deflect freely of the lens body, and therefore be liable to irritate portions of the eye in contact with the support structure. A variety of shapes and geometries for the lens supporting elements, or haptics, has been disclosed and described (U.S. Pat. No. 4,254,510; U.S. Pat. No. 4,363,143; U.S. Pat. No. 4,480,340; U.S. Pat. No. 4,504,981; U.S. Pat. No. 4,536,895; U.S. Pat. No. 4,575,374; U.S. Pat. No. 4,581,033; U.S. Pat. No. 4,629,460; U.S. Pat. No. 4,676,792; U.S. Pat. No. 4,701,181; U.S. Pat. No. 4,778,464; U.S. Pat. No. 4,787,902; U.S. Pat. No. Re. 33,039; U.S. Pat. No. 4,872,876; U.S. Pat. No. 5,047,052; U.K. Patent No. 2,165,456).

Despite the advances, there remain problems with intraocular implants. For example, when an intraocular lens is inserted in the eye, an incision is made in the cornea or sclera. The incision may cause the cornea to vary in thickness, leading to an uneven surface which can cause astigmatism. The insertion of a rigid lens through the incision, even with compressible haptics, requires an incision large enough to accommodate the rigid lens (typically at least 6 mm), and carries with it the increased risk of complications, such as infection, laceration of the ocular tissues, and retinal detachment. Deformable intraocular lenses made from polymethylmethacrylate (e.g. “PMMA”), polysulfone, silicone or hydrogel may be inserted through a smaller incision, about 4 mm.

It is preferred that the intraocular lens be capable of insertion through a small incision. U.S. Pat. No. 4,451,938 shows an intraocular lens in which the lens body is made in two pieces so that each piece may be inserted through the incision separately and then joined by dowels after insertion in the eye. U.S. Pat. No. 4,769,035 discloses a foldable lens which may be inserted through an incision about 3.5 mm in length.

When the intraocular lens is inserted in the anterior chamber of the eye, the feet of the haptics, or lens supporting elements, generally lodge in the scleral sulcus, a depression anterior to the scleral spur where the iris and the ciliary muscle join the sclera in the angle of the anterior chamber. The scleral sulcus is crossed by trabecular tissue in which are located the spaces of Fontana. The anterior chamber of the eye is filled with the aqueous humor, a fluid secreted by the ciliary process, passing from the posterior chamber to the anterior chamber through the pupil, and from the angle of the anterior chamber it passes into the spaces of Fontana to the pectinate villi through which it is filtered into the venous canal of Schlemm. The lens should be positioned so the flow of fluid through the trabecular tissue is not blocked or glaucoma may result.

Since the feet of the haptics of anterior chamber lenses rest in the scleral sulcus, the flow of fluid is blocked where the feet are in contact with the trabecular tissue. It is therefore desirable to decrease the amount of surface area of the haptic foot in contact with the trabecular tissue. At the same time, the haptic feet have sufficient height to prevent adhesive tissue or synechia from growing around the feet and anchoring them to the iris or cornea. The opening of the trabecula is about 200 microns, and the haptic feet of conventional intraocular lenses are usually on the order of 175 to 200 microns, effectively blocking the openings in the trabecula wherever the feet are in contact with the tissue.

Other lenses that are situated in the posterior chamber may attach to the ciliary sulcus or be positioned in the equator of the capsular sac. In haptics with attachment to the ciliary sulcus, appropriate dimensioning is essential to ensure proper anchoring. In haptics with attachment to the capsular equator, recent science demonstrates the need for appropriate dimensioning also, as the haptic must place the lens properly in the capsule. If the haptic is too short for the capsule, the lens can dislodge or rotate in the eye, events that can require additional surgery to correct and can also cause intraocular trauma. Additionally, haptics that are too short for the capsule do not allow the lens to provide the patient with any desired or designed focal flexibility (that is, accommodation). If the haptic is too long for the capsule, the lens can angle either posteriorly or anteriorly at a greater angle than designed, in the former case significantly reducing visual acuity at distance and risking reverse accommodation, in the latter case putting pressure on the iris and diminishing focal flexibility.

U.S. Pat. Nos. 5,258,025 and 5,480,428 describe a lens surrounded by a sheet-like “positioner” having projections called “supporting elements either at the four corners of or continuously around the positioner, the supporting elements being 0.3 mm long and 0.01 to 0.05 mm thick (7″a and 7″b of FIG. 3 of the '025 patent, 18 of the '428 patent). However, the lens is for implantation in the posterior chamber, the lens of the '428 actually having a length short enough to “float.” In addition, the sheet-like nature of the positioner prevents independent deflection of the feet in response to forces applied by the eye.

In addition, the lens may place a greater or lesser degree of force on the haptic feet as the lens is compressed, depending upon construction of the lens. Since the amount of pressure for a given surface area is proportional to the force, it is desirable to decrease or distribute the amount of force placed on the haptic feet in order to diminish the force applied by the feet on the trabecular tissue. This goal is achieved by mounting the haptic arms on the ends of a flexible support bar in cantilever fashion, the support bar being offset from the lens body by a stem.

The act of surgically removing the natural lens and replacing it with an intraocular lens of whatever design gives rise to certain other possible conditions that can have a profound impact on the patient's ability to see clearly over a protracted period of time, the extent of focal accommodation that can be provided to the patient, and the effective positioning of the replacement lens in the eye. These conditions normally occur in a majority of cases but may be able to be mitigated with inventive lens and haptic designs. In particular, ophthalmologists have observed that the lens capsule will tend to atrophy over time. This is in part attributable to the fact that the replacement lens rarely occupies the entire lens capsule, and most lenses tend to flatten out the capsule, thus allowing the anterior and posterior surfaces of the capsule to adhere together, causing capsular atrophy, hardening, and adhesions. All these will necessarily diminish the effectiveness of any lens claiming to offer focal accommodation. It is possible that increased circulation of the aqueous humor can preserve the suppleness of the natural lens capsule, and preventing contact between the capsular surfaces should prevent capsular adhesions.

Some physicians have advocated the use of capsular retention rings to prevent capsular atrophy. However, these rings, which are situated in the lens equator and generally used only during the surgical procedure, do not allow the ciliary body to influence the dimensions of the lens so as to provide for focal accommodation. Thus, whereas capsular retention rings may be effective when used in conjunction with non-accommodating lenses, their value with premium lenses that claim accommodation is questionable.

In some cases post surgical adhesions can occur between the lens capsule and the haptic of the intraocular replacement lens. If significant enough, these adhesions can diminish the focal accommodative functions of the lens.

Posterior Capsule Opacification (PCO) is a condition that occurs in approximately 50% of cataract patients within three years after surgery. PCO is caused by the natural migration of epithelial cells from the anterior lens capsule to the equator, thence to the posterior surface. Once the epithelial cells reach the equator, the cells die off leaving proteins that accumulate on the posterior capsular surface in the form of Elschnig's pearls or of fibroblasts that athere to the capsule and can cause significant fibroblasts, shrinkage, and clouding of the lens. If the PCO migrates to the optical area of the capsule, vision is significantly impaired. The occurrence of PCO can be mitigated surgically by means of Nd-YAG-Laser correction, which perforates the posterior capsule with small holes that deter the PCO from further migration. However, Nd-YAG laser capsulotomy surgery also carries risks of post-surgical complications including possible incursion of the vitreous into the capsule, and, as such, should be avoided if possible.

In the case of the inventive haptic designs incorporated herein, the inventors believe that the onset of PCO may be delayed or eliminated altogether through the use of appropriate haptic design to deter epithelial cell migration. In particular, 1) the design of an ultra-thin fixation plate and its appropriate sizing to fit securely at the capsular equator is intended to arrest epithelial cell migration at the haptic attachment zone and mitigate PCO accordingly, 2) a haptic design that keeps the capsule open and prevents contact between the anterior and posterior surfaces may assist in mitigating PCO onset by maintaining hydration of the capsule, 3) the quality of the cataract or CLEAR surgery can assist in retarding PCO through assiduous cleaning and polishing of the anterior capsule, and 4) the positioning of certain retention rings in the capsule, whether at the capsular equator, against the surface of the anterior capsule, and/or against the surface of the posterior capsule may arrest the migration of epithelial cells and prevent their aggregation in the posterior capsular optic zone. In some cases, IOL designers have found some success at mitigating the onset of PCO by configuring the posterior surface of the lens so as to provide a right angle at the junction of the lens with the posterior capsule. This configuration is particularly applicable for those lenses that rest entirely against the posterior capsule and do not accommodate. In other cases, IOL designers have determined that the surface quality of the haptic may have some influence on PCO mitigation.

SUMMARY OF THE INVENTION

The present invention overcomes the problems and disadvantages associated with current strategies and designs and provides new haptic devices and methods for positioning an intraocular lens in the eye, as well as designs for specific functionality to provide optimal focal flexibility and mitigate common post surgical problems.

One embodiment of the invention is directed to haptic devices that attach to the side of an edge of a lens and at a distance from the center of the lens. Preferably the haptic has a first haptic contact point that breaks the plane of a line passing through the center of the lens at about preferably 60 degrees from preferably the twelve o'clock position of the lens and a second haptic contact point that breaks the plane of a line passing through the center of the lens at about preferably 300 degrees from the twelve o'clock position of the lens. Preferably, the haptic arm center line is an extension of the planes passing through the lens at 60 and 300 degrees and extends to intersect a circle where the center is the center of the lens and the radius is greater than the radius of the lens. Also preferably, a radially distant end connects to an arm that intersects the outside diameter of the haptic at an offset point parallel to the 12 o'clock plane of the lens.

Preferably, the haptic is designed to affix to the lens on each side of the optic edge at a sixty degree angle from the center meridian of the lens. The haptic arm is a band of the haptic material that extends outward from the optical connection then curves back inward to connect with a solid arc of haptic material concentric with the optical edge of the lens and at a distance from such optical edge to provide for a kidney-shaped open section between the lens and such haptic material. The material of the haptic is preferably flexible, thus the haptic design provides for greater thickness of the haptic in the anterior/posterior plane so as to allow for suitable positioning of the lens in the eye without anterior-posterior dislocation. The ends of the haptic may be solid, with the fixation portion of the haptic thinner or thicker than the band of material at the optical connection. Additionally, the design of the haptic at its fixation point to the capsule is intended to allow the anterior and posterior rim of the capsule to fixate to the haptic at such point(s), thus inhibiting the migration of epithelial cells from the anterior to the posterior capsule, thereby mitigating Posterior Capsule Opacification. In another embodiment, the arms of the haptic are modestly arched to increase focal flexibility.

Another embodiment of the invention is directed to haptic devices that are kidney shaped, wherein a portion of the haptic end is solid. Preferably, the solid portion of the end is thinner than the remaining portion of the haptic. The haptic may further comprise a notch at the 12 o'clock position radially proximal that allows for bending. The functionality of the inventive haptic is to anticipate natural post-surgical capsular atrophy while maintaining both a firm attachment of the haptic at the capsular equator and central positioning of the lens optic in the capsule.

Another embodiment of the invention is directed to haptic devices that are kidney shaped, wherein a portion of the haptic end is solid. Preferably, the solid portion of the haptic is configured so as to extend forward to meet the anterior capsule at some distance from the equator, and posteriorly to meet the posterior capsule also at some distance from the equator. The haptic may further comprise a notch at the 12 o'clock position radially proximal that allows for bending. The haptic may also comprise a series of small notches at the inner radius of the anterior and/or posterior feet to allow for flexing in natural response to motions of the ciliary body as well as natural differences in capsular size. The functionality of the inventive haptic is to mitigate the onset of natural post-surgical capsular atrophy by maintaining the capsule open at the equator. This should provide for enhanced circulation in the capsule of aqueous solution, which may maintain suitable levels of hydration to preserve capsular flexibility. This also may inhibit the tendency of the anterior and posterior capsules to adhere to each other, a common post-surgical occurrence with other haptic designs. Another functionality of the inventive haptic is to provide positioning of the haptic feet so as to respond to the natural flexing and stretching of the lens capsule in response to ciliary body actions, while maintaining both a firm attachment of the haptic to the capsule, and central positioning of the lens optic in the capsule.

Another embodiment of the invention is directed to haptic devices that have some open sections between the haptic feet and the optic and with haptic feet that comprise rings, arced anteriorly and posteriorly with respect to the plane of the lens optic, such that the anterior ring makes contact with the anterior capsule at some distance from the lens equator, and the posterior ring makes contact with the posterior capsule at some distance from the lens equator, the rings connected to each other and to the framework supporting the lens optic by means of ribbons and struts that maintain suitable spacing between the rings and provide for proper positioning of the lens within the capsule. The functionality of the anterior ring is to arrest epithelial cell migration across the anterior capsule, thus preventing these cells from maturing and arriving at the capsular equator. Another functionality of the inventive anterior ring is to respond to the changes of the ciliary body in such a manner as to enable the forward motion of the lens optic within the capsule to accommodate for near vision. The functionality of the posterior ring is to protect the posterior optic zone from PCO by maintaining a suitable barrier between any pearls or fibroblasts that may develop over time and block their incursion into the area behind the lens optic. Another functionality of the posterior ring is to capture the physical forces fo the ciliary body and work in conjunction with the anterior ring, the struts and the ribbons of the haptic to allow the lens optic to move within the capsule to adjust to the various stages of focal accommodation. Another functionality of the posterior ring, together with the anterior ring, the struts and ribbons is to maximize the natural circulation of the aqueous humor so as to preserve hydration throughout the lens capsule and the aqueous humor. This hydration may have the additional desirable effect of providing a mechanism whereby the spent and arrested epithelial cells can be flushed away by the aqueous humor and disposed of through the trabecular meshwork.

Another embodiment of the inventive haptic is a solid circle haptic into which are cut arced channels, preferably five, that extend from the anterior ring to the edge of the optic. These channels allow the optic to move in accommodation without distortion or decentralization, while the anterior and posterior haptic rings fix the lens centered in the capsule and maintain the capsule open.

Another embodiment of the invention is directed to haptic design to work with injectors for surgically injecting the lens and haptic into an eye of a patient. Preferably the patient is a mammal and more preferably the mammal is a human. The haptic to be injected is capable of being compressed to allow insertion into the eye. Preferably, an outer portion of the haptic is compressed into a pointed shape to aide travel through an injector and entry into the eye, and a flexible portion is thicker in the anterior or posterior plane and allows the haptic to flex for positioning within the eye without anterior/posterior movement. Also preferably, the top of the proximal end of the solid portion is attached to the bottom of the haptic portion creating an offset between the solid and flexible portions of the haptic. The distal end is capable of resting in the equator of the capsule when inserted into the eye that contained the natural lens and the posterior zonules of the eye rest against the capsule. Once position in the eye, the force created by the movement of the ciliary processes of the eye is capable of moving the zonules toward a prime meridian of the eye, the zonules in turn transfer force through the capsule that contained the natural lens and to the end of the solid portion of the haptic. The haptic is preferably capable of transferring force to the end of the flexible portion of the haptic, where the offset creates an upward, rotational force along the haptic, in turn advancing the lens forward within the eye. Also preferably, the top of the proximal end of the solid portion is attached to the bottom of the haptic portion creating an offset between the solid and flexible portions of the haptic. The distal end is capable of resting against the anterior surface of the capsule when inserted into the eye that contained the natural lens and the posterior end rests against the posterior surface of the capsule. Once positioned in the eye, the force created by the movement of the ciliary processes of the eye is capable of moving the zonules toward a prime meridian of the eye, the zonules in turn transfer force through the capsule that contained the natural lens and to the end of the haptic feet. The haptic is preferably capable of transferring this force through a series of struts that connect the anterior ring to the posterior ring and to the end of the flexible portion of the haptic, where the offset creates a forward, force along the haptic, in turn advancing the lens forward within the eye.

Another embodiment of the inventive haptic is to provide for a series of easements in the struts connecting the anterior and posterior haptic rings whereby the level of force exercised on the lens is commensurate with the desired degree of accommodative movement of the lens within the eye.

Another embodiment of the invention is directed to a haptic of the invention and further comprising a second haptic to be localized 180 degrees from the first haptic when inserted into the eye. Preferably the lens and the haptic are essentially in the same anterior posterior plane. When positioned in the eye, forward movement of the lens creates the ability to see near objects from a single focal plane lens. When the lens is positioned anteriorly to the distal end of the haptics, it creates a positive vault, and when positioned posteriorly to the distal end of the haptics, it creates a negative vault.

Another embodiment of the invention is directed to a haptic, wherein a portion of the haptic is flexible and arched when inserted into an eye to where the zonules of the eye transfer force against the solid portion of the haptic creating an upward force vector, which in turn would move the lens optic anteriorly. If the haptic is a plat haptic at its contact point with the lens equator, there is a reduced amount of clearance between the anterior and posterior surfaces of the natural lens capsule allowing the surfaces to grow together. In this case, the attached capsular surfaces and the edge of the haptic form an opening small enough to significantly reduce cell migration from the equatorial region of the capsule. If the haptic used has anterior and posterior rings, there is a stable amount of clearance between the anterior and the posterior surfaces of the lens capsule preventing the surfaces from growing together. The angle of the negative vault and the angle of the radius between the prime meridian and the optic edge are preferably equal. Also preferably, equal angles create a tangent between the capsule that contained the natural lens and the edge of the optic of the lens. When inserted into the eye, tangential forces use the capsule to seal the edge of the lens preventing cell migration under the lens.

Another embodiment of the invention is directed to a haptic wherein sections of the haptic are angled and connected by joints such that the optic rests posteriorly in the capsule for distance vision and the joints, flexing or stretching in response to the movement of the ciliary body, moves the lens anteriorly for near vision. Preferably, there are rings attached to the angled joints or segments that rest on the anterior and/or posterior surfaces of the capsule, maintaining a distance between such anterior and posterior surfaces thereby providing for continuous natural hydration of the capsule and circulation of the natural fluids of the aqueous humor. Also preferably, such rings arrest substantially the migration of epithelial cells on the anterior capsule and the proliferation of posterior capsular opacification in the focal range of the lens.

Another embodiment of the invention is directed to a method of securing a lens in a mammalian eye comprising removing a natural lens from a mammalian eye; and inserting a lens comprising the haptic of the invention into the mammalian eye.

Another embodiment of the invention is directed to devices, such as insertion devices, and methods of inserting a haptic into a lens envelope of a mammalian eye comprising the haptic of the invention.

Other embodiments and advantages of the invention are set forth in part in the description, which follows, and in part, may be obvious from this description, or may be learned from the practice of the invention.

DESCRIPTION OF THE DRAWINGS

FIG. 1. Top view of lens with haptic.

FIG. 2. Sagittal view of lens with haptic.

FIG. 3. Ciliary process for distance vision.

FIG. 4. Ciliary process for near vision.

FIG. 5. Lens with arched haptic.

FIG. 6. Thin edge impedes posterior capsular opacification.

FIG. 7. Cross sectional area of haptic end.

FIG. 8. Area of connection between haptic and lens to be enlarged.

FIG. 9. Enlarged area of connection between haptic and lens.

FIG. 10. Top View of Lens with haptic comprising curved ribbons to form the kidney shape.

FIG. 11. Sagittal view of curved-open haptic in distance position.

FIG. 12. Sagittal view of haptic with curved loops in near accommodation position.

FIG. 13. Second iteration of curved ribbon (open looped) haptic in distance position.

FIG. 14. Second iteration of curved ribbon (open looped) haptic in near accommodation position.

FIG. 15. Third iteration of open looped haptic in distance position.

FIG. 16. Third iteration of open looped haptic in near accommodation position.

FIG. 17. Second iteration of open loop kidney ribbon haptic.

FIG. 18. Fourth iteration of haptic in distance position.

FIG. 19. Fourth iteration of haptic in near position.

FIGS. 20a-b. Fifth iteration of open looped haptic with anterior and posterior feet in initial design specifications.

FIG. 21. Fifth iteration of open loop haptic in distance position.

FIG. 22. Fifth open loop haptic in near accommodation position.

FIGS. 23a-b. Open Loop Haptic Design (Kidney haptic) with full anterior and posterior Rings.

FIGS. 24a-b. Full circle haptic with arced grooves.

 DESCRIPTION OF THE INVENTION

The haptic device is used to affix an intraocular lens within the lens capsule once the natural crystalline lens has been removed surgically. The three specific design purposes of the haptic are: i) to permit the lens to be implanted in the eye by means of a special injector through an incision of less than about 3 mm; ii) to allow the lens to move within the posterior chamber of the eye in order to provide focal flexibility to the patient; and iii) to affix the lens in the equator of the lens capsule in such a way as to minimize the risk of Posterior Capsule Opacification (“PCO”), a negative consequence of lens replacement procedures that currently occurs in approximately 50% of patients within 2 to 3 years after surgery. Although intraocular lenses have been successfully implanted for several decades now, many of the haptic designs do not produce the desired results of mitigating PCO and/or facilitating focal flexibility (or the ability of the patient to adjust far to near vision and minimize the need for reading glasses).

A haptic device design has been surprisingly discovered that that ameliorates PCO and facilitates focal flexibility (or the ability of the patient to adjust far to near vision and minimize the need for reading glasses). In one embodiment, the haptic of the invention is secured to the equator of the lens capsule by means of a solid but very thin plate of the same material as the attached lens, which preferably may be any of polymethylmethacrylate, hydrophobic or hydrophilic acrylate, silicone, or blends of these materials (or of the same material as the lens). The width of the plate is designed to extend beyond that portion of the lens envelope that typically closes post-removal of the natural lens (FIG. 7). Epithelial cells, normally found on the anterior surface of the inner lens capsule, can migrate to the posterior surface if their path is not impeded. A purpose of the design of the haptic of the invention is to cause a tighter closure at the edge of the haptic, which inhibits ongoing migration and growth of the epithelial cells. Moreover, the width and breadth of that portion of the haptic helps preclude migration of such epithelial cells across the anterior portion of the lens capsule to the equator. While this design may not altogether remove the risk of PCO, it retards PCO growth substantially.

A second haptic device design has been surprisingly discovered that that ameliorates PCO and facilitates focal flexibility (or the ability of the patient to adjust far to near vision and minimize the need for reading glasses). In one embodiment, the haptic of the invention is secured to the anterior capsule with an arced anterior foot, and to the posterior capsule with an arced posterior foot the effect of which is to maintain a space between the anterior capsule and the posterior capsule so as to provide for ongoing hydration of the lens capsule by the fluids of the aqueous humor. The connection between the arced anterior foot and the arced posterior foot is made by a series of struts, which may have some easements cut into them, that maintain the desired distance between the anterior and posterior feet of the haptic and optimize the accommodative force on the optic of the inventive lens, while providing for adequate fluid circulation within the capsule and the posterior chamber of the aqueous humor. Epithelial cells, normally found on the anterior surface of the inner lens capsule, can migrate to the posterior surface if their path is not impeded.

In another embodiment (depicted in FIGS. 23a-b), a haptic design has been surprisingly discovered that has anterior 2335 and posterior 2330 haptic feet that comprise entire rings that rest on the anterior and posterior capsules, respectively, maintaining the entire capsule open and creating a barrier at both the anterior and the posterior capsular surfaces to prevent migration of epithelial cells. In this embodiment, the haptic feet are connected by a series of struts 2315 that have open spaces 2320 between, preserving the designed distance between the rings and providing for optimal fluid circulation around the inventive lens. In this embodiment also, the anterior 2335 and posterior 2330 rings may be configured so as to arrest epithelial cell migration across the anterior capsule and incursion of PCO into the optical zone of the posterior capsule, thereby providing the potential for the patient to use the intraocular lens for a substantial period of time without adverse consequences. In this embodiment, easements may be made in the struts to accommodate smaller than normal capsules, thus providing for stable concentration of the lens optic notwithstanding potential capsular size differences or changes over time. In this embodiment additionally certain easements may be made in the inner surface of the anterior 2335 and posterior 2330 rings so as to provide for responsiveness of the lens haptic to the muscular prompts of the ciliary body.

In another embodiment, the haptic of the invention may be constructed principally of a ribbon of the same material as the attached lens (as described herein). The open framework design of this portion of the haptic is to hold the optic centered vis-à-vis the retina while responding to the motion of the ciliary body so as to move the optic forward and backward in the eye, much in the same manner as a natural lens, with a minimum of lateral or oblique distortion. In the variation of this haptic design as set forth in FIG. 5, the arched portion of the haptic further facilitates the focal flexibility and causes the optic of the lens to move anteriorly as the patient focuses on near objects.

In these embodiments, the entire dimension of the lens, including both haptics and the optic, preferably varies depending upon the measurement of the natural lens capsule. The haptic has varying points of individual tailoring, including the length of the ribbon haptic (2) and (3), and the dimension of the solid end portion of the haptic. Additionally, the haptic may be used for veterinary purposes, and its overall dimensions may be increased or reduced to fit in the lens capsule of various animals.

The following examples illustrate embodiments of the invention, but should not be viewed as limiting the scope of the invention.

EXAMPLES

Depicted in FIG. 1 is a top view of an intraocular lens with a haptic device, and FIG. 2, a sagittal view. The haptic attachment point 8 to optic is shown along with a ribbon shaped haptic extension 9 which is in a plane through the center of the optic and the attachment point. The ribbon shaped haptic arm intersection with a circular plane larger than the radius of the optic. The solid end portion of the haptic 13 intersects the outside diameter of the lens at a point that is parallel to a plane passing through the 12 o'clock and 6 o'clock positions of the lens. The overall shape of the haptic resembles a kidney with sharper curves where the lens optic makes up a portion of the kidney. Solid end portion 13 of the haptic is thinner than the ribbon shaped sections 9.

As depicted in FIG. 1, ribbon shaped haptic 9 lies between the solid portion 13 and the end of the extended arm 8. The ribbon shaped section of the haptic 9 is shown above the solid portion of the haptic 13 in FIG. 2. Also, along the bottom, the ribbon shaped haptic 9 attaches to the solid haptic 13 along the edge (proximal to the optic) of solid portion of the haptic 13. FIG. 1 shows the notch 16 which is cut into solid haptic portion 13 to allow easy flexing for deformation into an injector.

As depicted in FIG. 3, the tip 17 of the lens haptic rests against the equator of the capsule which is held in position by the zonules. Zonules are the hair like structures that attach to the natural lens and the ciliary body and hold the natural lens in position. Zonules also aide in changing the shape of the natural lens for near vision. FIG. 3 also depicts the capsule 19 from which the natural lens was removed, and the ciliary body 20 of the eye that changes shape to allow the natural lens to change shape to give the patient near vision. The cornea 21 is the clear portion of the eye that refracts (bends) light. Along with the natural lens the light is bent to come to focus on the retina. The iris (colored portion) of the eye is used to meter the amount of light allowed in the eye.

As depicted in FIG. 3, the intraocular lens in the far position in the eye 23, whereas in FIG. 4, the ciliary body 24 moves and changes shape to provide near vision so that the intraocular lens is in the near position 25 in the eye.

FIG. 5 depicts an arched haptic 26. As the ciliary body move force is applied to the tip of the haptic, which is transmitted into the arched haptic, which forces the haptic to compress and move anteriorly.

As depicted in FIG. 6 is one embodiment of the haptic device and optic lens, demonstrating that area of the haptic (A-A) further delineated in FIGS. 7, 8 and 9, specifically designed to mitigate PCO. FIG. 6 addresses the circular formation, described by a continuation of the indicated arc ascribed to the haptic plate, indicating an approximation of the capsular equator and the lens position within the capsule.

Depicted in FIG. 7 is a cross-sectional area of the haptic end. Shown are the anterior section of the natural lens 27, the posterior section of the natural lens 28, and the intraocular lens haptic thin solid end portion 29.

Depicted in FIG. 8 are the anterior and posterior sections of the natural lens capsule as they grow together after surgery. Depicted in FIG. 9 is an enlarged portion of FIG. 8, showing the remaining tissue 30 surrounding the lens solid end 31 section stretched tight. The small opening remains 32 whereby cell growth movement through the opening is impeded. With thick footplates in many cases the opening is large enough that there is little or no impediment to the cell migration; therefore, the cells deposit between the intraocular lens and the posterior capsule which opacifies the capsule and reduces the light passage.

Depicted as FIG. 10 is a top view of a haptic in which the angles have been removed providing for a continuous kidney shape in which the width of the ribbon haptic is less than the depth of that haptic so as to provide for natural easement and constant centering of the lens optic while ensuring sufficient thrust strength to move the optic anteriorly and posteriorly within the capsule to provide focal accommodation. FIGS. 11 and 12 are sagittal views of such a lens haptic, demonstrating a haptic design that is configured with two angles, as in a knee and an ankle, that respond to the force of the ciliary muscles to flex and extend, thus moving the lens optic.

As depicted in FIGS. 13 and 14, the innovative haptic contains one or more angled or arced segments providing additional flex and thrust for moving the lens within the eye to adjust for distance and near vision. The dimensions of the angled segments may vary in accordance with the designed purpose, and may be constructed such that the width of the segments may be varied or consistent while the depth of the segments will vary according to stress calculations for that segment such that the joints of the segments flex adequately to allow the length of the segments to exert the required force on the lens optic.

As depicted in FIGS. 15 and 16, the innovative haptic contains a knee and is designed such that the posterior foot of the haptic rests somewhat more central than the connection point of the knee with the anterior capsule.

FIG. 17 illustrates a further embodiment of the kidney haptic, with FIGS. 18 and 19 demonstrating the sagittal views of such haptic, in which case the anterior haptic plate is configured to curve anteriorly toward the center of the eye. The posterior foot of the haptic rests against the posterior capsule at a certain point somewhat outside the comparable contact point of the anterior haptic, though dimensions may vary in accordance with the designed purpose of such lens.

FIGS. 20a-b depict a further modification of the kidney haptic, showing a top view (FIG. 20a) and a sagittal view (FIG. 20b) with preliminary dimensions. FIGS. 21 and 22 illustrate the functionality of this inventive haptic in positions for distance and near vision.

In all of the above design manifestations, rings may also be affixed to the anterior and or posterior joints or legs of such angled segments to rest in the capsule at some distance from the equator, or with one ring in the equator and the other at some distance, to mitigate the migration of epithelial cells. In such cases the rings may contain right angles at the areas of contact with the anterior or posterior surface of the capsule. The function of such rings in conjunction with the angled segments may also be to maintain the aperture of the lens capsule distant from the equator so as to provide for continuous irrigation of the region by the normal circulation mechanisms of the aqueous humor. This may preserve the natural consistency and elasticity of the lens capsule, thus ensuring prolonged functionality of the inventive lens haptic.

FIGS. 23a-b depict both top 2300 and sagittal 2305 views of a full circular haptic with ribbons 2310 and struts 2315 to create oval openings 2320 between the optic 2325 and the haptic rings. The number of contained ovals and the precise configuration of such ovals may vary according to the designed intent of the inventive haptic. For example, as depicted in FIG. 23a, there may be five equally sized and equally spaced struts, wherein the width (measured radially on the haptic) of the ovals defined by the struts are smaller than the length of the ovals (measured circumferentially on the haptic).

FIGS. 24a-b depict top and sagittal views, respectively, of a full circular haptic with arced grooves of material removed so as to provide for focal flexibility and fluid flow. In this case the number of grooves and the length and configuration of such grooves may vary in accordance with the intended purpose of the designed haptic.

Other embodiments and uses of the invention will be apparent to those skilled in the art from consideration of the specification and practice of the invention disclosed herein. All references cited herein, including all publications, U.S. and foreign patents and patent applications, are specifically and entirely incorporated by reference. The term comprising, where ever used, is intended to include the terms consisting and consisting essentially of. Furthermore, the terms comprising, including, and containing are not intended to be limiting. It is intended that the specification and examples be considered exemplary only with the true scope and spirit of the invention indicated by the following claims.

Claims

1. A haptic of an intraocular lens comprising:

a single solid annular ribbon adapted to be placed within a capsular bag of an eye;
a plurality of struts directly coupled to both the annular ribbon and a circumference of a single optic, wherein the annular ribbon and the optic are coaxial and the annular ribbon is positioned at a distance from the circumference of the optic, wherein the plurality of struts define openings between the annular ribbon and the circumference of the optic, each opening having a smaller radial width than circumferential length; and
wherein the annular ribbon is comprised of an anterior haptic ring coupled to the plurality of struts, and a posterior haptic ring directly coupled only to the anterior haptic ring at an apex of a U-shaped recess in a radially outermost circumferential surface of the annular ribbon, wherein each of the anterior and posterior haptic rings is annular at the radially outermost circumferential surface, and wherein the posterior haptic ring is coupled posteriorly to the anterior haptic ring.

2. The haptic of claim 1, wherein an angle between each of the plurality of struts is 60 degrees.

3. The haptic of claim 1, wherein an angle between each of the plurality of struts is 72 degrees.

4. The haptic of claim 1, wherein the plurality of struts define ovular openings between the optic and the annular ribbon.

5. The haptic of claim 4, wherein there are five ovular openings.

6. The haptic of claim 1, wherein an inner radius of the annular ribbon is greater than the outer radius of the optic.

7. The haptic of claim 6, wherein each of the plurality of struts connects a point on an outside diameter of the optic to a point on an inside diameter of the anterior haptic ring.

8. The haptic of claim 1, which is capable of being compressed by an instrument to allow insertion into the eye.

9. The haptic of claim 8, wherein an outer portion of the haptic is compressible into a pointed shape to aide travel through an injector and entry into the eye.

10. The haptic of claim 1, wherein a number of struts of the plurality of struts is greater than or equal to five.

11. The haptic of claim 1, wherein a number of struts is less than five.

12. The haptic of claim 1, further comprising easements between the plurality of struts to reduce a mass of each of the plurality of struts.

13. The haptic of claim 1, wherein the haptic rings are positionable anteriorly or posteriorly within the capsular bag.

14. The haptic of claim 1, wherein the anterior haptic ring is positioned anteriorly from an anterior surface of the optic.

15. The haptic of claim 1, wherein, when inserted in the eye, a distal end of the haptic rests at an equator of the capsular bag.

16. The haptic of claim 1, wherein the annular ribbon, when inserted into the eye, is capable of moving in response to movement of a ciliary process.

17. The haptic of claim 16, wherein movement of the annular ribbon provides focal accommodation.

18. The haptic of claim 1, wherein, when inserted into the eye, the haptic significantly reduces cell migration from an equatorial region of the capsular bag in comparison to an intraocular lens without the haptic.

19. The haptic of claim 1, wherein the posterior haptic ring is a flange extending from the anterior haptic ring.

20. The haptic of claim 1, wherein the posterior haptic ring is capable of being coupled posteriorly to the anterior haptic ring prior to and post insertion into the eye.

21. A method of replacing a natural lens of a mammalian eye comprising:

removing the natural lens from the mammalian eye; and
inserting into the mammalian eye the haptic of claim 1.

22. A haptic of an intraocular lens comprising:

a single solid annular ribbon adapted to be placed within a capsular bag of an eye;
a plurality of struts directly coupled to both the annular ribbon and a circumference of a single optic, wherein the annular ribbon and the optic are coaxial and the annular ribbon is positioned at a distance from the circumference of the optic, wherein the plurality of struts define ovular openings between the annular ribbon and the circumference of the optic, each opening having a smaller radial width than circumferential length; and
wherein the annular ribbon is comprised of an anterior haptic ring coupled to the plurality of struts, and a posterior haptic ring directly coupled only to the anterior haptic ring at an apex of a U-shaped recess in a radially outermost circumferential surface of the annular ribbon, wherein each of the anterior and posterior haptic rings is annular at the radially outermost circumferential surface, and wherein the posterior haptic ring is coupled posteriorly to the anterior haptic ring.
Referenced Cited
U.S. Patent Documents
3673616 July 1972 Fedorov et al.
3866249 February 1975 Flom
3906551 September 1975 Otter
3913148 October 1975 Potthast
3975779 August 24, 1976 Richards et al.
4014049 March 29, 1977 Richards et al.
4053953 October 18, 1977 Flom et al.
4073014 February 14, 1978 Poler
4087866 May 9, 1978 Choyce et al.
4092743 June 6, 1978 Kelman
4102567 July 25, 1978 Cuffe et al.
4136406 January 30, 1979 Norris
4141973 February 27, 1979 Balazs
4159546 July 3, 1979 Shearing
4173281 November 6, 1979 Trought
4174543 November 20, 1979 Kelman
4190049 February 26, 1980 Hager et al.
4198980 April 22, 1980 Clark
4215440 August 5, 1980 Worst
4240163 December 23, 1980 Galin
4242760 January 6, 1981 Rainin
4244060 January 13, 1981 Hoffer
4249271 February 10, 1981 Poler
4251887 February 24, 1981 Anis
4254509 March 10, 1981 Tennant
4254510 March 10, 1981 Tennant
4269307 May 26, 1981 LaHaye
4270230 June 2, 1981 Poler
4280232 July 28, 1981 Hummel
4285072 August 25, 1981 Morcher et al.
4325375 April 20, 1982 Nevyas
4326306 April 27, 1982 Poler
4349027 September 14, 1982 DiFrancesco
4363142 December 14, 1982 Meyer
4363143 December 14, 1982 Callahan
4366582 January 4, 1983 Faulkner
4370760 February 1, 1983 Kelman
4377329 March 22, 1983 Poler
4409691 October 18, 1983 Levy
4423809 January 3, 1984 Mazzocco
4435855 March 13, 1984 Pannu
4441217 April 10, 1984 Cozean, Jr.
4446581 May 8, 1984 Blake
4451938 June 5, 1984 Kelman
4463458 August 7, 1984 Seidner
4468820 September 4, 1984 Uhler et al.
4480340 November 6, 1984 Shepard
4494254 January 22, 1985 Lopez
4504981 March 19, 1985 Walman
4508216 April 2, 1985 Kelman
4517295 May 14, 1985 Bracke et al.
4527294 July 9, 1985 Heslin
4530117 July 23, 1985 Kelman
4534069 August 13, 1985 Kelman
4536895 August 27, 1985 Bittner
4573998 March 4, 1986 Mazzocco
4575374 March 11, 1986 Anis
4576607 March 18, 1986 Kelman
4581033 April 8, 1986 Callahan
4585456 April 29, 1986 Blackmore
4591358 May 27, 1986 Kelman
4608049 August 26, 1986 Kelman
4615703 October 7, 1986 Callahan et al.
4619256 October 28, 1986 Horn
4624669 November 25, 1986 Grendahl
4629460 December 16, 1986 Dyer
4634423 January 6, 1987 Bailey, Jr.
4638056 January 20, 1987 Callahan et al.
4655775 April 7, 1987 Clasby, III
4676792 June 30, 1987 Praeger
4676794 June 30, 1987 Kelman
4684014 August 4, 1987 Davenport
4687484 August 18, 1987 Kaplan
4700638 October 20, 1987 Przewalski
4701181 October 20, 1987 Arnott
4704123 November 3, 1987 Smith
4710195 December 1, 1987 Giovinazzo
4710795 December 1, 1987 Nippert et al.
4711638 December 8, 1987 Lindstrom
4718906 January 12, 1988 Mackool
4736836 April 12, 1988 Alongi et al.
4764169 August 16, 1988 Grendahl
4769035 September 6, 1988 Kelman
4778464 October 18, 1988 Sergienko et al.
4781719 November 1, 1988 Kelman
4787902 November 29, 1988 Sheets et al.
4795460 January 3, 1989 Anis
4795462 January 3, 1989 Grendahl
4804361 February 14, 1989 Anis
4816032 March 28, 1989 Hetland
4828558 May 9, 1989 Kelman
4834750 May 30, 1989 Gupta
4842600 June 27, 1989 Feaster
RE33039 August 29, 1989 Arnott
4852566 August 1, 1989 Callahan et al.
4863462 September 5, 1989 Fedorov et al.
4863463 September 5, 1989 Tjan
4863465 September 5, 1989 Kelman
4871363 October 3, 1989 Kelman
4872876 October 10, 1989 Smith
4878911 November 7, 1989 Anis
4888012 December 19, 1989 Horn
4919130 April 24, 1990 Stoy et al.
4923296 May 8, 1990 Erickson
4932966 June 12, 1990 Christie
4932970 June 12, 1990 Portney
4950290 August 21, 1990 Kamerling
4994080 February 19, 1991 Shepard
4995714 February 26, 1991 Cohen
5002568 March 26, 1991 Katzen
5019098 May 28, 1991 Mercier
5047052 September 10, 1991 Dubroff
5076684 December 31, 1991 Simpson et al.
5098444 March 24, 1992 Feaster
5100226 March 31, 1992 Freeman
5108429 April 28, 1992 Wiley
5118452 June 2, 1992 Lindsey et al.
5123905 June 23, 1992 Kelman
5133747 July 28, 1992 Feaster
5133749 July 28, 1992 Nordan
5152789 October 6, 1992 Willis
5166711 November 24, 1992 Portney
5171320 December 15, 1992 Nishi
5176686 January 5, 1993 Poley
5178636 January 12, 1993 Silberman
5192319 March 9, 1993 Worst
5197981 March 30, 1993 Southard
5199559 April 6, 1993 Dark
5229797 July 20, 1993 Futhey et al.
5236452 August 17, 1993 Nordan
5258025 November 2, 1993 Fedorov et al.
5266074 November 30, 1993 Nishi et al.
5281227 January 25, 1994 Sussman
5361780 November 8, 1994 Kellan
5366501 November 22, 1994 Langerman
5370652 December 6, 1994 Kellan
5405386 April 11, 1995 Rheinish et al.
5425734 June 20, 1995 Blake
D360068 July 11, 1995 Hambleton et al.
5443506 August 22, 1995 Garabet
5468246 November 21, 1995 Blake
5476512 December 19, 1995 Sarfarazi
5476514 December 19, 1995 Cumming
5480428 January 2, 1996 Fedorov et al.
5489302 February 6, 1996 Skottun
5496366 March 5, 1996 Cumming
5507806 April 16, 1996 Blake
5522890 June 4, 1996 Nakajima et al.
5549670 August 27, 1996 Young et al.
5593436 January 14, 1997 Langerman
5628794 May 13, 1997 Lindstrom
5643275 July 1, 1997 Blake
D382399 August 19, 1997 Hambleton et al.
5674282 October 7, 1997 Cumming
5682223 October 28, 1997 Menezes et al.
5697973 December 16, 1997 Peyman et al.
5709220 January 20, 1998 Kellan
5713958 February 3, 1998 Weiser
5772667 June 30, 1998 Blake
5782911 July 21, 1998 Herrick
5800532 September 1, 1998 Lieberman
5847802 December 8, 1998 Menezes et al.
5855605 January 5, 1999 Herrick
5919229 July 6, 1999 Portney
5928282 July 27, 1999 Nigam
5947976 September 7, 1999 Van Noy et al.
5976150 November 2, 1999 Copeland
6010510 January 4, 2000 Brown
6013101 January 11, 2000 Israel
6015435 January 18, 2000 Valunin et al.
6051024 April 18, 2000 Cumming
6083261 July 4, 2000 Callahan et al.
6090141 July 18, 2000 Lindstrom
6096077 August 1, 2000 Callahan et al.
6110202 August 29, 2000 Barraquer et al.
6120148 September 19, 2000 Fiala et al.
6129723 October 10, 2000 Anderson
6142999 November 7, 2000 Brady et al.
6152958 November 28, 2000 Nordan
6197059 March 6, 2001 Cumming
6203549 March 20, 2001 Waldock
6224628 May 1, 2001 Callahan et al.
6241777 June 5, 2001 Kellan
6261321 July 17, 2001 Kellan
6277146 August 21, 2001 Peyman et al.
6299641 October 9, 2001 Woods
6398786 June 4, 2002 Sesic
6443985 September 3, 2002 Woods
6447519 September 10, 2002 Brady
6461384 October 8, 2002 Hoffmann
6488707 December 3, 2002 Callahan et al.
6488709 December 3, 2002 Barrett
6494911 December 17, 2002 Cumming
6517577 February 11, 2003 Callahan et al.
6533813 March 18, 2003 Lin et al.
6537283 March 25, 2003 Van Noy
6605093 August 12, 2003 Blake
6622855 September 23, 2003 Callahan et al.
6623522 September 23, 2003 Nigam
6645246 November 11, 2003 Weinschenk, III
6666887 December 23, 2003 Callahan et al.
6749633 June 15, 2004 Lorenzo
6786928 September 7, 2004 Callahan et al.
6797004 September 28, 2004 Brady
6800091 October 5, 2004 Callahan et al.
6921415 July 26, 2005 Callahan et al.
6976989 December 20, 2005 Vincent
7037328 May 2, 2006 Vincent
7037338 May 2, 2006 Nagamoto
7063723 June 20, 2006 Ran
7125422 October 24, 2006 Woods
7179292 February 20, 2007 Worst
7198640 April 3, 2007 Nguyen
7220279 May 22, 2007 Nun
7223288 May 29, 2007 Zhang
7279006 October 9, 2007 Vincent
7354451 April 8, 2008 Koch
7503938 March 17, 2009 Phillips
7713299 May 11, 2010 Brady et al.
8043372 October 25, 2011 Bumbalough
20010001836 May 24, 2001 Cumming
20010012964 August 9, 2001 Lang
20010044657 November 22, 2001 Kellan
20010044857 November 22, 2001 Pham et al.
20020055777 May 9, 2002 Cumming et al.
20020072673 June 13, 2002 Yamamoto
20020072795 June 13, 2002 Green
20020095212 July 18, 2002 Boehm
20020103536 August 1, 2002 Landreville et al.
20020116059 August 22, 2002 Zadno-Azizi et al.
20020120331 August 29, 2002 Galin et al.
20020161437 October 31, 2002 Zhou et al.
20020193877 December 19, 2002 Hoffmann et al.
20030033013 February 13, 2003 Callahan
20030050695 March 13, 2003 Lin et al.
20030065387 April 3, 2003 Callahan et al.
20030078655 April 24, 2003 Callahan
20030114927 June 19, 2003 Nagamoto
20030130732 July 10, 2003 Sarfarazi
20030135272 July 17, 2003 Brady et al.
20030135273 July 17, 2003 Callahan
20030149479 August 7, 2003 Snyder et al.
20030149480 August 7, 2003 Shadduck et al.
20040215340 October 28, 2004 Messner et al.
20040230300 November 18, 2004 Bandhauer et al.
20040236423 November 25, 2004 Zhang et al.
20040249456 December 9, 2004 Cumming
20050033308 February 10, 2005 Callahan
20050107875 May 19, 2005 Cumming
20050251253 November 10, 2005 Gross
20060047339 March 2, 2006 Brown
20060047340 March 2, 2006 Brown
20060100704 May 11, 2006 Blake et al.
20060142781 June 29, 2006 Pynson et al.
20060235515 October 19, 2006 Chassain
20060247767 November 2, 2006 Koch
20060293694 December 28, 2006 Futamura
20070093892 April 26, 2007 Mackool
20070129799 June 7, 2007 Schedler
20070135915 June 14, 2007 Klima
20070156236 July 5, 2007 Stenger
20070239274 October 11, 2007 Kellan
20070260309 November 8, 2007 Richardson
20080161913 July 3, 2008 Brady et al.
20080281417 November 13, 2008 Nagamoto
20090125106 May 14, 2009 Weinschenk et al.
20090171458 July 2, 2009 Kellan et al.
20090248031 October 1, 2009 Ichinohe et al.
20100131059 May 27, 2010 Callahan et al.
20100131061 May 27, 2010 Callahan et al.
20100179652 July 15, 2010 Yamamoto
20100204787 August 12, 2010 Noy
20100204788 August 12, 2010 Van Noy
20100228260 September 9, 2010 Callahan et al.
20110054600 March 3, 2011 Bumbalough
20110191086 August 4, 2011 Callahan
20110257742 October 20, 2011 Bumbalough
20110313522 December 22, 2011 Hayes
20110313523 December 22, 2011 Hayes
20120010704 January 12, 2012 Bumbalough
20120078363 March 29, 2012 Lu
20120330415 December 27, 2012 Callahan et al.
Foreign Patent Documents
1961399 April 1991 EP
2029235 March 1980 GB
2124500 February 1984 GB
2165456 April 1986 GB
61502661 November 1985 JP
6055131 December 1985 JP
2003533274 November 2003 JP
WO98/17205 April 1998 WO
WO99/29266 June 1999 WO
WO00/78252 December 2000 WO
WO03017867 June 2003 WO
WO2004082535 September 2004 WO
WO2007117476 October 2007 WO
WO2007134019 November 2007 WO
WO2008108523 September 2008 WO
WO2008108524 September 2008 WO
Other references
  • Chinese Office Action for Chinese Application 200780020967.4 dated Apr. 12, 2011.
  • Austria Examination Report for Austrian Application 200807369-4 dated Mar. 10, 2010.
  • PCT Search Report for PCT/US2009/065955 dated May 31, 2011.
  • PCT Patentability Report for PCT/US2009/065955 dated Jan. 27, 2010.
  • PCT Search Report for PCT/US2009/065960 dated Jan. 27, 2010.
  • PCT Patentability Report for PCT/US2009/065960 dated Jan. 27, 2010.
  • PCT Search Report for PCT/US2007/008328 dated Jun. 19, 2008.
  • PCT Patentability Report for PCT/US2007/008328 dated Jun. 19, 2008.
  • PCT Search Report for PCT/US2008/088430 dated Aug. 11, 2009.
  • PCT Patentability Report for PCT/US2008/088430 dated Aug. 11, 2009.
  • PCT Search Report for PCT/US2010/026230 dated May 19, 2010.
  • PCT Patentabilty Report for PCT/US2010/026230 dated May 19, 2010.
  • PCT Search Report for PCT/US2006/16221 dated May 10, 2007.
  • PCT Patentability Report for PCT/US2006/16221 dated May 10, 2007.
  • PCT Search Report for PCT/US2011/37583 dated Nov. 15, 2011.
  • PCT Patentabilty Report for PCT/US2011/37583 dated Nov. 15, 2011.
  • Zaldivar et al,; “The Current Status of Phakic Intraocular Lenses;” International Opthamology Clinics; vol. 36, No. 4; 1996; pp. 107-111.
  • Neuhann; “Corneal or Lens Refractive Surgery?” Journal of Refractive Surgery; vol. 14; May/Jun. 1998; pp. 272-279.
  • Rosen et al.; “Staar Collamer Posterior Chamber Phakic Intraocular Lens to Correct Myopia and Hyperopia;” J. Cataract Refract. Surg.; vol. 24; May 1998; pp. 596-606.
  • Sanders et al; “Implantable Contact Lens for Moderate to High Myopia: Phase 1 FDA Clinical Study with 6 Month Follow-Up;” J. Cataract Refract Surg.; vol. 24; May 1998; pp. 607-6111.
  • PCT Search Report for PCT/US2010/026230, dated May 19, 2010.
  • PCT Patentability Report for PCT/US2010/026230, dated May 19, 2010.
  • PCT Patentability Report for PCT/US2009/065955, dated Jan. 27, 2010.
  • PCT Search Report for PCT/US2009/065955, dated Jan. 27, 2010.
  • Japan Office Action for Japanese Application 2009-504268, dated Apr. 24, 2012.
  • Chinese Decision of Rejection for Chinese Application 200780020967.4, dated May 28, 2012.
  • Australian Examination Report for Austrian Application 2009319753, dated Aug. 29, 2012.
  • PCT Search Report and Patentability Report for PCT/US12/40732, dated Sep. 18, 2012.
  • CA Office Action for Application No. 2,744,859, dated Sep. 11, 2012.
  • PCT Search Report for PCT/US2012/072014, dated Mar. 8, 2013.
Patent History
Patent number: 9439755
Type: Grant
Filed: Nov 25, 2009
Date of Patent: Sep 13, 2016
Patent Publication Number: 20100131061
Assignee: Anew IOL Technologies, Inc. (Bristol, TN)
Inventors: Wayne B. Callahan (Abingdon, VA), Paul S. Koch (Warwick, RI), Anna S. Hayes (Newton Centre, MA), Robert E. Kellan (Methuen, MA)
Primary Examiner: Andrew Iwamaye
Assistant Examiner: Leslie Lopez
Application Number: 12/626,473
Classifications
Current U.S. Class: Eye Contact (351/159.02)
International Classification: A61F 2/16 (20060101);